EP0051026A1 - Taschenrechner zum Messen von Strahlung mit einem Halbleiterdetektor mit elektronischer Energiekompensation - Google Patents

Taschenrechner zum Messen von Strahlung mit einem Halbleiterdetektor mit elektronischer Energiekompensation Download PDF

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Publication number
EP0051026A1
EP0051026A1 EP81401663A EP81401663A EP0051026A1 EP 0051026 A1 EP0051026 A1 EP 0051026A1 EP 81401663 A EP81401663 A EP 81401663A EP 81401663 A EP81401663 A EP 81401663A EP 0051026 A1 EP0051026 A1 EP 0051026A1
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EP
European Patent Office
Prior art keywords
detector
radiation
energy
dose
nuclear
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP81401663A
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English (en)
French (fr)
Inventor
Robert Allemand
Michel Laval
Pierre Parot
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Commissariat a lEnergie Atomique et aux Energies Alternatives CEA
Original Assignee
Commissariat a lEnergie Atomique CEA
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from FR8022814A external-priority patent/FR2492989A1/fr
Priority claimed from FR8105754A external-priority patent/FR2502342A1/fr
Application filed by Commissariat a lEnergie Atomique CEA filed Critical Commissariat a lEnergie Atomique CEA
Publication of EP0051026A1 publication Critical patent/EP0051026A1/de
Withdrawn legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/02—Dosimeters
    • G01T1/026—Semiconductor dose-rate meters
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/15—Instruments in which pulses generated by a radiation detector are integrated, e.g. by a diode pump circuit

Definitions

  • the present invention relates to a portable computing device for measuring radiation using a radiation detector and electronically compensating for the hypersensitivity of this detector to low energy radiation; this detector is preferably a semiconductor detector. Electronic compensation makes it possible to accurately measure the dose integrated into the radiation over time. This device allows direct visualization of the integrated dose. In addition, this portable device can deliver an alarm signal for a dose rate given to said radiation. This portable device is particularly applicable in the field of radiation protection.
  • the subject of the invention is a portable calculation device produced in large series, such as mini-calculators, on which we add a "nuclear detection” function allowing the measurement of radiation.
  • This computing device provided with its “nuclear detection” function makes it possible to remedy the drawbacks mentioned and in particular makes it possible to more simply and more completely compensate for the hypersensitivity of the detector to low energy radiations.
  • the invention therefore relates to a portable computing device comprising in known manner means for adding digital information, means for determining time periods and display means, characterized in that it also comprises a nuclear detector capable of delivering electrical signals whose amplitude spectrum depends unequivocally on the energy spectrum of the radiation in which it is placed and means for converting these signals into digital information, the addition means receiving said information digital, the means for determining time periods controlling said adding means so as to calculate the dose of radiation received during a period of time, called integration, which is displayed by said display means.
  • This dose corresponds to the dose of radiation received by human tissues when these are located near the detector.
  • the computing device comprises electronic means for compensating for the sensitivity of the detector as a function of the energy of the radiation so as to make it identical to that of human tissue, so that the detector produces an output signal which is in a constant relationship with the energy of said radiation which can be absorbed by human tissue.
  • a detector whose response is in a constant relationship with the energy absorbed by human tissues for the radiation considered is called a "tissue equivalent” detector. It should be noted that in the invention, the detector is made “fabric equivalent” thanks to the electronic processing of the signals which it supplies.
  • the detector is a semiconductor crystal detector such as for example cadmium telluride or silicon.
  • the portable device further comprises a nuclear filter, constituting an absorbent screen.
  • the calculation device comprises a "nuclear detection" function which allows the measurement of radiation.
  • This function is done by means of a portable device of the individual dosimeter type which we will first describe.
  • This portable device of the individual dosimeter type is shown diagrammatically in FIG. 1.
  • This portable device comprises a detector, for example with a semiconductor crystal 1 such as a crystal of cadmium or silicon telluride operating at ambient temperature.
  • a semiconductor crystal 1 such as a crystal of cadmium or silicon telluride operating at ambient temperature.
  • On the opposite faces 3 and 5 of the crystal detector 1 are arranged two metal electrodes 7 and 9 between which is established, by means of a power source a potential difference of the order of a few volts.
  • the semiconductor detector 1 can be associated with a set of absorbent screens 11, enveloping the detector and made of a material containing tin and lead, playing the role of nuclear filter similar to those used with Geiger-Muller counters and serving as precompensation of the energy of the radiation arriving on this detector.
  • the fact of completely enveloping the detector makes it possible to make the response of the detector isotropic, that is to say identical regardless of the side by which the radiation enters the detector.
  • Wedges such as 14 keep the crystal detector 1 in a housing 16 made of a light material which does not absorb radiation such as plastic or aluminum.
  • the conductivity induced in the semiconductor produces electrical signals whose amplitude spectrum is unequivocally dependent on the energy spectrum of said radiation. It should be noted that for a monoenergetic radiation, the signal supplied by the detector will not be unique, but will be composed of a spectrum whose shape will be unique and whose maximum amplitude will be proportional to the energy of the detected radiation.
  • the role of the electronic circuit 15, associated with the detector, is to process this signal so as to transform it into one or more quantities directly usable by the personnel, such as the dose rate and the integrated dose. These quantities are displayed on a liquid crystal display for example 17.
  • the electronics 15 control an audible alarm 19, triggering for a given digital threshold of dose rate or integrated dose of radiation thus allowing indicate the presence of radiation.
  • the use of a semiconductor material having a high number of Z electrons or atomic number means that the number of interactions with the material, for a flux y of given energy, will be much greater if this flux is weakly energetic. Indeed, for an energy flow E less than 250 KeV, the number of interactions follows the law of the photoelectric effect, that is to say, that the number of interactions is proportional to Z 5 ⁇ E -3.5 , and for an energy flow E between 250 keV and 1 MeV the number of interactions follows the law of the Compton effect, i.e. the number of interactions is proportional to ZE -1 .
  • this electronic compensation is possible because the spectral response of the detector, for example to a semiconductor crystal such as cadmium telluride or silicon, is a one-to-one function of the energy of the radiation. This compensation cannot be envisaged with dosimeters with Geiger-Muller since in this. In this case, the amplitude of the pulses is independent of the initial energy.
  • the semiconductor detector could be either cadmium telluride or silicon.
  • the silicon present on cadmium telluride has the advantage of being closer to a "tissue equivalent" response since the atomic number of silicon is lower than that of cadmium telluride, and therefore closer the average atomic number of human tissue.
  • silicon has the drawback of being able to be easily produced only in the form of small dimensions (5 ⁇ 5 mm 2 of surface over 0.5 mm of thickness); this limits its use to determining medium or high dose rates and integrated dose, that is to say greater than 10 bn / h.
  • Cadmium telluride although handicapped by a worse energy response, has the advantage of having a very good sensitivity, because it can be produced in the form of larger dimensions than those of silicon (5 ⁇ 5 ⁇ 5 mm 3 ). Furthermore, its radiation stopping power is very much higher than that of silicon because its atomic number and its density are higher than those of silicon.
  • Figures 2, 3 and 4 show two embodiments of the electronic circuits associated with the detector, for example a semiconductor crystal detector.
  • the means for processing the signal from the detector are of digital type.
  • the detector 1 is connected to the power source by means of re sistances R of high value, that is to say several tens of megohms.
  • the signal or pulse from detector 1, having a very low amplitude, must first be amplified by means of an amplification chain such as 21 before being compensated according to the invention.
  • This amplification chain can be constituted as shown in FIG. 3 by an amplifier A 1 with low background noise, operating as a charge preamplifier with a capacitance C 1 of 0.5 to 1 picofarad and a resistance R 1 such that R 1 C 1 is between 50 and 100 microseconds and by an amplifier A 2 mounted as a voltage amplifier by means of a resistor R 2 , the output of the amplifier A l being connected to the negative input of the amplifier A 2 by means of a resistor R 3 .
  • the electronic compensation means essentially comprise a shaping circuit 23 ensuring amplitude-time conversion and in parallel the "threshold" function by means of two resistors r 1 and r 2 , in order to eliminate the amplitude pulses too low to be taken into account and in particular the noise created by the leakage current of the crystal detector 1.
  • This shaping circuit connected to the output of the amplifier A 2 via a capacitor C 2 can be constituted by a T..S circuit. ( Figure 3) known as the Schmidt trigger and produces signals in the form of slots used to discharge the capacitance C 1 of the preamplifier A 1 .
  • the discharge of the capacitor C1 can be carried out by means of a feedback chain consisting of two resistors in series R 4 and R 6 mounted in a variable divider bridge so as to go rier the amplitude of the signal provided by the shaping circuit 23, and a resistor R 5 of high value, that is to say several tens of megohms.
  • This resistor R 5 converts the voltage of the slots provided by the shaping circuit 23 into a constant current which will be used to discharge the capacitor C 1 in a linear fashion.
  • Resistor R 6 therefore makes it possible to adjust the value of the discharge current of the capacitor C 1 , therefore the duration ⁇ T of this discharge.
  • This resistance R 6 is adjusted so that the discharge duration ⁇ T of the capacity C 1 is short compared to the duration R 1 C 1 , that is to say that ⁇ T is close to R 1 C 1 / 3, i.e. 10 to 13 microseconds.
  • the detector when a radiation is detected, supplies a quantity of charge Q which will charge the capacitor C 1 and give the output of the amplifier A 1 a voltage step ⁇ V equal to Q / C 1 that amplifier A 2 will reverse and amplify. If the amplitude of the voltage step exceeds the threshold of the shaping circuit 23 which is adjustable, the shaping circuit switches and, via the feedback chain R 4 , R 6 , R 5 discharges the capacitor C 1 until the output signal from the amplifier A 2 is zero, at this time, the shaping circuit 23 returns to its initial state, awaiting a new pulse.
  • the duration of the slot provided by the shaping circuit 23 is proportional to the energy of the ionizing radiation arriving on the crystal detector 1.
  • the feedback chain R 4 , R 6 , R 5 is connected at a point A located before an input capacitor C 3 connecting the detector 1 to the negative input of the preamplifier A 1 .
  • the pulse current flowing through the capacitor C 3 then has a zero mean value since the latter is crossed, in one direction by an amount of charge Q supplied by the crystal detector 1 and which is stored in the capacitor C l , then in the other direction by an amount of charge -Q supplied by the feedback chain.
  • the average potential of point A is constant regardless of the detector output signal.
  • the conversion in duration of the amplitude of the signals leaving the amplification chain 21 is linear, but we can envisage a non-linear amplitude-time conversion, according to a pre-established law allowing by example of associating a lower duration for low energy radiation than for high energy.
  • the signal from the shaping circuit 23 opens the door 25 of a counting scale 27 which counts the pulses from a clock 29 at a fixed frequency, for example of 1 MHz.
  • the counting scale 27 therefore provides an address for each detected event, for example between 1 and 10 corresponding to 10 classes of energy increasing from 1 to 10.
  • a memory 31 such as a memory programmable or reprogrammable with read only (PROM or REPROM) which attributes to each event, according to its address, therefore the class in which it is located, a predetermined value (ranging from 1 to 64 for example) so as to apply a higher weight to the higher class (10) therefore to give more weight to the high energies that '' at low energies, which makes it possible to compensate for the hypersensitivity of the detector at low energies, too many events detected by the low energy detector compared to human tissue being compensated by the allocation of a lower weight than that given high energy events.
  • PROM programmable or reprogrammable with read only
  • the result that is to say the integrated dose received by the detector, therefore consists in adding these successive values supplied by the memory 31, during each detected event, by means of an adder such as 33.
  • the final result is then displayed on the display 17.
  • the introduction of the memory 31 makes it possible to discretely carry out any law of compensation for the energy of the ionizing particles; this makes it possible to adapt to any volume and quality of the detector.
  • the choice of the weights to be assigned to the different energies is made with the detector itself which is irradiated, that is to say with a plurality of sources emitting known doses at each of the energies corresponding to the 10 classes used in the example of compensation, either by using a single broad spectrum source called "white in dose", that is to say emitting a constant number of mrd / h / keV over a range of energy corresponding to the response range of the measurement (for example from 50 keV to 3 MeV).
  • the first which requires as many sources as there are energy classes used for compensation, ie 10 in the example given above.
  • This white source irradiating the detector, the distribution of the amplitudes is measured, that is to say the spectral response of the detector excited by this white source.
  • a device known as a multichannel amplitude analyzer comprising at least as many channels as energy classes
  • the measuring device described above up to and including the counting scale 27 constitutes an amplitude encoder comprising a modest number of channels (10 in the example described), each event being coded at an address between 1 and 10.
  • This clock delivers a pulse sequence which would advantageously be of high frequency for 6 pulses for example, of frequency half for 2 pulses, then of frequency still of half for 2 other pulses, in the example of 10 energy classes.
  • the differences in responses between the detector, in particular with cadmium telluride and human tissues are large and rapidly variable in low energies, and are decreasing towards high energies. This therefore makes it possible to limit the number of classes while having a completely satisfactory energy analysis.
  • the means for amplifying and compensating for the electrical signal coming from the crystal detector 1 are of analog type. Such means are shown in FIG. 4.
  • the amplification and compensation means comprise a variable gain amplifier 35, that is to say that as a function of the amplitude of the signal output of the detector, depending on the energy of the radiation, the gain of the amplifier is modulated so as to give more weight to the strong pulses than to the weak ones.
  • the dose integrated in time can be displayed, as previously, on the display 17 via the adder 33, the counting scale 27 and an analog-digital converter 39 connected to the gain amplifier. 35.
  • the display of the integrated dose can be done analogically by replacing the counting scale 27 and the analog-digital converter 39 with an integrator giving directly the dose integrated over time.
  • a "nuclear detection" function has been added in portable computing devices such as mini-calculators or in watches by placing a semiconductor detector such as telluride in the portable device. cadmium or silicon and having the properties described above.
  • a semiconductor detector such as telluride
  • cadmium or silicon and having the properties described above.
  • the digital display could be used to display, the dose rate, the dose, the points of the spectrum in energy, etc ..., the integration and the counting will allow to calculate the integrated dose, the electronic stopwatch will allow calculate the dose rate and the waiting registers will make it possible to choose alarm thresholds (presence of radiation).

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Measurement Of Radiation (AREA)
EP81401663A 1980-10-24 1981-10-21 Taschenrechner zum Messen von Strahlung mit einem Halbleiterdetektor mit elektronischer Energiekompensation Withdrawn EP0051026A1 (de)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
FR8022814 1980-10-24
FR8022814A FR2492989A1 (fr) 1980-10-24 1980-10-24 Dispositif portatif de mesure de rayonnements ionisants utilisant un detecteur a semi-conducteur et a compensation electronique
FR8105754 1981-03-23
FR8105754A FR2502342A1 (fr) 1981-03-23 1981-03-23 Dispositif de calcul portatif permettant la mesure de rayonnements ionisants utilisant un detecteur a semi-conducteur et notamment a compensation electronique

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EP0051026A1 true EP0051026A1 (de) 1982-05-05

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2117900A (en) * 1982-03-25 1983-10-19 Michael Anthony Newell Radiation detector
FR2584815A1 (fr) * 1985-07-12 1987-01-16 Centre Nat Rech Scient Systeme de mesure de flux de photons gamma, x, de neutrons thermiques et/ou rapides
FR2598816A1 (fr) * 1986-05-14 1987-11-20 France Etat Armement Procede permettant d'assurer la compensation spectrale de detecteurs nucleaires a semi-conducteurs.
WO1995012868A1 (de) * 1993-11-03 1995-05-11 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Multifunktionssensoren in elektronischen produkten

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JPS6188175A (ja) * 1984-09-17 1986-05-06 Power Reactor & Nuclear Fuel Dev Corp 放射線用局部被曝警報装置
US4733383A (en) * 1986-09-16 1988-03-22 Waterbury Nelson J Combined digital and analog timepiece and radiation monitor assembly
US4751390A (en) * 1986-12-17 1988-06-14 The United States Of America As Represented By The United States Department Of Energy Radiation dose-rate meter using an energy-sensitive counter
EP0300054B1 (de) * 1987-02-02 1992-12-02 Hitachi, Ltd. Tragbares dosimeter sowie dessen verwendung bei einem gerät zur kontrolle intensiver strahlungsaussetzung
US5070878A (en) * 1988-11-14 1991-12-10 Neoprobe Corporation Detector and localizer for low energy radiation emissions
US5151598A (en) * 1987-03-17 1992-09-29 Neoprobe Corporation Detector and localizer for low energy radiation emissions
US4968898A (en) * 1987-10-12 1990-11-06 Jeol Ltd. Pulse shaping circuit for radiation detector
GB2364379B (en) * 1997-08-11 2002-03-13 Siemens Plc Personal radiation dosemeter with electromagnetic and radiological screening
USD424199S (en) * 1998-10-23 2000-05-02 United States Surgical Corporation Housing assembly for radiation detection
JP2004528568A (ja) * 2001-05-14 2004-09-16 デパートメント オブ アトミックエナジー、ガヴァメント オブ インディア 低コストデジタルポケット線量計
US6765214B1 (en) * 2002-02-13 2004-07-20 The United States Of America As Represented By The United States Department Of Energy Smart radiological dosimeter
WO2005003815A1 (en) * 2003-07-01 2005-01-13 Antanouski Aliaksandr Alexeevi Portable watch with radiation monitor
US7247855B2 (en) * 2004-03-09 2007-07-24 United States Of America As Represented By The Secretary Of The Army Portable nuclear detector
US8803089B2 (en) * 2012-06-01 2014-08-12 Landauer, Inc. System and method for wireless, motion and position-sensing, integrating radiation sensor for occupational and environmental dosimetry
CN104335071B (zh) * 2012-06-07 2016-09-28 国立大学法人静冈大学 放射线剂量计及放射线剂量的计算方法
EP3279695A4 (de) 2015-03-31 2018-08-08 Ingeniería Y Marketing, S.A. Dosimetrisches steuerungssystem

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US3646347A (en) * 1968-12-02 1972-02-29 Advanced Technology Center Inc Method and apparatus for measuring radiation
FR2314505A1 (fr) * 1975-06-12 1977-01-07 Materiel Telephonique Radiametre

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GB1559664A (en) * 1977-02-17 1980-01-23 Tokyo Shibaura Electric Co Semiconductor radiation detector
US4197461A (en) * 1978-08-17 1980-04-08 The United States Of America As Represented By The United States Department Of Energy Miniaturized radiation chirper
US4301367A (en) * 1980-01-21 1981-11-17 Hsu Sam S Radiation dosimeter

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US3541311A (en) * 1966-06-27 1970-11-17 Us Navy Nuclear radiation digital dose measuring system
US3646347A (en) * 1968-12-02 1972-02-29 Advanced Technology Center Inc Method and apparatus for measuring radiation
FR2314505A1 (fr) * 1975-06-12 1977-01-07 Materiel Telephonique Radiametre

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MEASUREMENT TECHNIQUES, vol. 18, no. 10, octobre 1975, NEW YORK (US) V.S. GOREV et al.: "Measurement of gamma-radiation exposure dose rate with an instrume nt incorporating a silicon detector", pages 1535-1536 *
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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2117900A (en) * 1982-03-25 1983-10-19 Michael Anthony Newell Radiation detector
FR2584815A1 (fr) * 1985-07-12 1987-01-16 Centre Nat Rech Scient Systeme de mesure de flux de photons gamma, x, de neutrons thermiques et/ou rapides
FR2598816A1 (fr) * 1986-05-14 1987-11-20 France Etat Armement Procede permettant d'assurer la compensation spectrale de detecteurs nucleaires a semi-conducteurs.
WO1995012868A1 (de) * 1993-11-03 1995-05-11 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Multifunktionssensoren in elektronischen produkten

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